Wire-free, dual-mode calibration instrument for high energy therapeutic radiation

ABSTRACT

An instrument for checking quality of therapeutic x-ray and electron radiation provides modes optimized for both electrons and for photons obtained by physically flipping the unit to interpose the necessary build-up material between the radiation beam and contained detectors. The invention provides an improved method of constructing ionization detectors for improved energy discrimination using such detectors and wire-free operation.

CROSS-REFERENCE TO RELATED APPLICATIONS

This patent application is a continuation-in-part of U.S. patent application Ser. No. 10/774,817, filed Feb. 9, 2004, and hereby incorporated by reference.

STATEMENT REGARDING FEDERALLY SPONSORED RESEARCH OR DEVELOPMENT

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BACKGROUND OF THE INVENTION

The present invention relates to quality assurance instruments for medical radiotherapy equipment used for radiation treatment of tumors or the like.

Cancerous tumors may be treated by irradiating the tumor with high-energy photons or electrons (henceforth both termed “radiation”).

Such radiotherapy relies in part on the fact that tumor tissue is more sensitive than normal tissue to such high-energy radiation. Nevertheless, the radiation dose must be carefully controlled to limit the exposure of healthy tissue while ensuring sufficient radiation is received by the tumor.

Radiation dose may be controlled by a variety of means including shutters for collimating the radiation beam to the area of the tumor, filters for varying the intensity of radiation within the area of the tumor, and control of the exposure duration. An accurate understanding of the energy, flux, and alignment of the radiation beam is essential for such control. Generally, as is understood in the art, radiation energy describes the average energy of the individual photons or electrons whereas radiation flux is number of electrons or photons per unit area per unit time.

Radiation energy may be determined by calculating changes in flux at two depths within a homogenous medium, for example, a water phantom.

Radiation flux is normally determined using an ionization chamber or semiconductor detector placed in the radiation beam at a fixed distance from the radiation source. A “build-up” material such as a plastic block may be placed in front of the flux-detector to improve its sensitivity. For the purposes of periodic quality assurance of a radiotherapy machine, the output of the flux-detector may be compared to a base line for the same detector. In this way, precise calibration of the detector to a standard is not required.

Radiation alignment is normally determined with respect to a visible light field projected along with the radiation showing, for example, an illuminated rectangular area and/or cross-hair pattern. Alignment may be verified by exposing a film marked to show the location of the light field or crosshairs and comparing the exposed film to the markings. Alternatively, as shown in U.S. Pat. No. 4,988,866, a fixture having multiple ionization detectors and multiple light detectors (also called edge detectors) may be used, and the signals from the ionization detectors and light detectors may be compared.

It is desirable that the radiation therapy machine be checked on a frequent, periodic basis at each of its settings. Such quality assurance checks can be cumbersome and time consuming particularly when multiple pieces of test equipment must be used, for example, as would be required to calibrate a radiotherapy machine that provides both electron beams and photon beams at a variety of energy levels. It is difficult to construct a quality assurance instrument that works for a wide variety of different radiation energies and different radiation modes, e.g. electrons or photons, equally well.

BRIEF SUMMARY OF THE INVENTION

The present invention provides a radiation beam checker that may verify flux profiles and constancy for a wide variety of radiation energies and modes. Several features contribute to this versatility. First, the beam checker may receive radiation from either of two directions, flipping to receive electrons through one side and photons through the other. In this way, a single set of detectors may be optimized for either of two different radiation modes. Second, rather than relying on a single filtered and unfiltered detector to determine energy level, the present invention may use multiple detectors, each having a different filtration to provide data for a more sophisticated energy discrimination function accurate over a wide energy range. Visual fiducia on both surfaces of the beam checker allow alignment to be determined by flux measurements from the multiple flux-detectors without the need for photosensitive edge detectors that would be required on both surfaces.

One embodiment of the present invention permits wire-free operation simplifying manipulation of the beam checker without requiring radio communication that may be difficult to establish in the environment of the radiotherapy machine. An additional feature of one embodiment of the present invention is automatic linkage of data to energy levels to minimize necessary operator input. In one embodiment, the present invention may employ a new construction technique for ionization detectors simplifying the manufacture and improving the consistency of multi-detector systems.

Specifically then, the present invention may provide a test apparatus for both photon and electron radiation, the test apparatus having a housing providing opposed first and second faces holding a set of detectors between the first and second faces. In this embodiment, a first calibrating material for electrons is positioned to intercept electrons passing through the first face to the detectors, and a second calibrating material for photons is positioned to intercept photons passing through the second face to the detectors.

It is thus one feature of at least one embodiment of the invention to provide a single test unit that may be tailored to two modes of radiation by placing different build-up or filter materials on the opposite faces of the housing and flipping the housing according to the radiation mode.

The test apparatus may include a quantitative radiation measurement display on a third face of the housing visible when either the second or first face is lying on the surface. The display may change orientation according to whether electrons or photons are being measured to be upright to an operator in either mode.

Thus, it is another feature of at least one embodiment of the invention to provide a device that retains ease of use in either orientation of the housing.

One embodiment the invention provides a wire-free test apparatus for therapeutic radiation systems having a housing holding a set of radiation detectors for measuring radiation flux at predetermined locations and a solid state memory for receiving and storing the radiation flux measurements. A battery within the housing powers the radiation detectors and solid-state memories and a port is provided on the housing for downloading the stored radiation flux measurements to a remote computer.

Thus, it is another feature of at least one embodiment of the invention to provide an easily maneuverable test device unencumbered by connecting cables. It is another feature of at least one embodiment of the invention to provide wire-free operation without the need for radio transmission of data such as can be blocked by the shielding used around radiotherapy machines.

The housing may include a light field guide on its surface, delineating a region of the housing containing the detectors that should be exposed to radiation. The processing circuitry and memory may be within the housing outside of the region.

Thus, it is another feature of at least one embodiment of the invention to provide a simple method of minimizing radiation exposure to solid-state memory which is normally sensitive to radiation damage or interference.

The processing circuitry contained within the housing may communicate with at least some of the radiation detectors to detect the start of a new radiation measurement from signals produced by the radiation detectors and to automatically store the radiation measurements in the solid state memory.

Thus, it is another feature of at least one embodiment of the invention to provide for simplified data acquisition without the need for complex keyboard control or a permanently attached remote terminal.

In one embodiment, the invention provides a beam checker for therapeutic radiation comprising a set of spaced radiation flux-detectors producing flux signals and at least one radiation energy-detector providing an energy signal and a storage system for storing a set of energy ranges. Processing circuitry compares at least one of the flux signals to benchmark flux values of an energy range corresponding to the energy signal to provide an indication of any improper operation of the measured radiation source. Generally, the benchmark flux values may indicate flatness, symmetry, or constancy over time.

Thus, it is a feature of at least one embodiment of the invention to use the energy signal to automatically relate flux measurements to proper benchmark measurements for different energy ranges.

The radiation energy-detector may be a set of at least three detector elements having different filtrations to provide radiation signals and the energy signal may be derived from an algebraic combination of the radiation signals from the set of detector elements. Alternatively or in addition, the radiation detector may be a set of detector elements, at least one of which element has a “backscatter element” positioned behind it with respect to the measured radiation so that the detector element is sensitive to backscatter, and the energy signal may be derived from an algebraic combination of the radiation signals.

Thus it is one feature of at least one embodiment of the invention to provide an improved low-profile energy sensor that works over a wider range of energy values than can be achieved with a single filtered detector.

One embodiment of the invention provides an ionization detector that includes a front and rear plate positioned on a front and rear side of a volume of ionizable gas or other fluid to receive a voltage thereacross to collect the charges resulting from radiation ionizing the gas. The rear plate may be formed of a printed circuit board providing a collector on its front surface and multiple layers, including a middle layer providing a signal trace and a first and second ground flanking the middle layer, where the signal trace may connect to the collector.

Thus it is an feature of at least one embodiment of the invention to provide improved manufacturability for ionization detectors by using the fabrication techniques associated with printed circuit boards while providing the shielding needed to protect the faint ionization signals.

These particular objects and advantages may apply to only some embodiments falling within the claims and thus do not define the scope of the invention.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a perspective view of the beam checker of the present invention as held in a cradle prior to use showing a first side for receiving photon radiation;

FIG. 2 is a perspective view of the beam checker and cradle (in partial phantom) together with various cables, a remote computer, and charging unit as may be used with the beam checker; and showing a second side for receiving electron radiation;

FIG. 3 is a front elevational view of a third wall of the beam checker of FIGS. 1 and 2 as supports a display of radiation energy such as may flip in orientation, depending on the particular radiation mode being detected;

FIG. 4 is a fragmentary view of a printed circuit board positioned beneath the target markings of the units of FIGS. 1 and 2, the printed circuit board providing a number of detectors for measuring radiation flux and/or energy;

FIG. 5 is a cross-sectional view through several detectors of FIG. 4 and front and rear buildup materials of the housing showing passage of electron radiation and photon radiation through different build-up materials (for all detectors) and different filtration materials (for particular detectors) and a backscatter material (for one detector);

FIG. 6 is an exploded perspective view of one of the detectors of FIG. 4 showing its assembly from a cap placed on exposed traces of a printed circuit board;

FIG. 7 is a perspective cross-sectional view of the assembled ionization detector FIG. 6 showing the multiple layers of the printed circuit board used to provide shielding of the detected signals;

FIG. 8 is a block diagram of the circuitry of the detector of FIG. 1, such as may be placed on the circuit board of FIG. 4 and which employs a microprocessor based processing system to store data within an associated memory for later communication through a port;

FIG. 9 is a flow diagram showing the calculation of energy for electron radiation;

FIG. 10 is a figure similar to that of FIG. 9 showing the calculation of energy for photon radiation;

FIG. 11 is a flow chart of a program executed by the microprocessor of the circuit of FIG. 8 in implementing the present invention;

FIG. 12 is a fragmentary perspective view of an alternative embodiment of the ionization detector of FIG. 6 using a continuous front plate instead of a cap; and

FIG. 13 is a figure similar to that of FIG. 12 showing depressions formed in the front plate to provide improved focus of the field lines.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENT

Referring now to FIG. 1, the beam checker 10 of the present invention provides a mobile detecting unit 12 having a generally rectangular, box-shaped housing 20 providing a first photon-receiving face 16 opposed to a second electron-receiving face 18.

Referring also FIG. 2, a portion of the photon-receiving face 16 and electron-receiving face 18 is marked with a target 22 defining an area of radiation exposure and thus providing a means for aligning the housing 20 of the mobile detecting unit 12 with a light field or laser crosshair provided by standard radiotherapy machines, as will be described. Typically, the target 22 or 22′ is 20 cm by 20 cm and includes a crosshair dividing the target area into equal quadrants.

Referring to FIGS. 2 and 3, a first side wall 24 of the housing 20 holds a three-character, 1.2 inch tall, seventeen-segment light emitting diode (LED) alphanumeric display 26, a reset button 28 and a separate bicolor LED 29, radiation mode captions and lamps 30, and a mode select button 32. During operation, side wall 24 remains visible when either of the photon-receiving face 16 or electron-receiving face 18 of the housing 20 are supported by structure of the radiation therapy machine, for example, a horizontal patient support 34.

When photon-receiving face 16 is against the patient support 34, electron-receiving face 18 is upward facing a source of radiation along axis 36. The operator may then press the mode select button 32 to illuminate a lamp next to the radiation mode caption denoting “electron” and to indicate to the beam checker 10 that this is the type of radiation being measured. The caption “electron” will be right side up when the housing 20 is appropriately oriented for receiving electron radiation.

Upon exposure of the beam checker 10 to electron radiation, the alphanumeric display 26 will display a detected energy range using both alphabetic and numeric characters. Typically, the energy ranges will include 6E, 9E, 12E, 16E, and 22E. The number being a measure of energy in MeV and the “E” suffix indicates that the beam checker 10 is checking for electron radiation. The alphanumeric display will be automatically oriented to be right side up, based on the mode selected, when the beam checker is correctly positioned to receive electron radiation as described. This reorientation requires simply a change in the mapping of segments of the alphanumeric display 26 and can be accomplished electronically by the contained processor described below.

The housing 20 may be flipped as shown by arrow 38 so that photon-receiving face 16 is upward to receive a beam of photons along axis 40. The operator may then press the mode select button 32, but this time to illuminate a lamp next to the radiation mode caption denoting “photon” and to indicate to the beam checker 10 that this is the type of radiation being measured. The caption “photon” is inverted with respect to the caption “electron” to be right side up when the housing 20 is appropriately oriented for receiving photon radiation.

Upon exposure of the beam checker 10 to photon radiation, the alphanumeric display 26 will display a detected energy range using both alphabetic and numbers typically 6X, 18X or 23X with the number being a measure of energy in MV and the “X” suffix indicates that the beam checker 10 is checking for x-ray photons. As before, the alphanumeric captions will be automatically oriented to be right side up based on the mode selected. Thus it will be understood that the alphanumeric display 26, reset button 28, LED 29, radiation mode captions and lamps 30, and a mode select button 32 may be readily used with either orientation of the housing 20.

Referring again to FIGS. 1 and 2, a second side wall 42 of housing 20 of the beam checker 10, spanning electron-receiving face 18 and photon-receiving face 16, provides on its surface a data/power connector 44, a data-only connector 45, and power connector 46. When the mobile detecting unit 12 is placed within the cradle 14, the sidewall 42 abuts an upper face 48 of the cradle 14 so that data/power connector 44 connects with a corresponding data/power connector 52 and power connector 54 on the upper face 48 of the cradle 14. In this way, data may be communicated to and from the mobile detecting unit 12 and power may be provided to the mobile detecting unit 12.

The mobile detecting unit 12 is held in position on the cradle 14 by two guiding pylons 50 extending upward from the cradle 14 and abutting the electron-receiving face 18 and photon-receiving face 16. Note that in FIG. 2 one guiding pylon 50 is removed for clarity.

The cradle 14 includes provisions to receive a power cord 58 which may provide line power from a standard wall transformer 59, or the like, to the mobile detecting unit 12 through power connector 54. Alternatively, the power cord 58 may be received directly by the mobile detecting unit 12 at power connector 46.

Cradle 14 also incorporates two RS-232 connectors 60 and 62 which electrically communicate with data/power connector 52 (connector 60 is opposite connector 62 and not visible in FIG. 2). Connectors 60 and 62 allow the mobile detecting unit 12 to be connected to the cradle 14 by means of a standard RS-232 cable 64 connecting between RS-232 connector 60 and data/power connector 44 on the mobile detecting unit 12 when mobile detecting unit 12 is not sitting on the cradle 14. Connector 62 allows a second cable 66 to connect the cradle 14 (via connector 62) to an independent programming and data-logging computer 68, or the like and thereby connect through data/power connector 52 with the mobile detecting unit 12. Alternatively, the computer 68 may communicate directly with the mobile detecting unit 12 via cable 66 attaching to data connector 45.

Generally, a direct connection between the computer 68 and mobile detecting unit 12 will be used only during an initial calibration procedure when constant reference to the computer 68 will be required. For all other times, the mobile detecting unit 12 will communicate with the computer 68 (for example during periodic downloading of data) via the cradle 14 and the joining of data/power connectors 44 and 52. While mobile detecting unit 12 is in the cradle 14, the mobile detecting unit 12 may exchange data with the computer 68 and may receive power for operation and for charging internal batteries as will be described.

Referring now to FIGS. 1 and 4, positioned within the housing 20 parallel to, and centered between, photon-receiving face 16 and electron-receiving face 18 is a printed circuit board 70 having a detector zone 72 located beneath the targets 22 and 22′. Positioned on the printed circuit board 70 and centered in the detector zone 72 is a central detector 74 a. Positioned on either side of detector 74 a along a longitudinal axis of the printed circuit board 70 are detectors 74 b and 74 c whereas positioned on either side of detector 74 a along a lateral axis of the printed circuit board 70 are detectors 74 d and 74 e. Detector 74 b, 74 c, 74 d, and 74 e are located at midpoints between detector 74 a and the edge of the radiation field as defined by the targets 22 and 22′.

Detectors 74 a-74 e detect radiation flux and may be, for example, ionization detectors, solid-state detectors, or other detector types known in the art. Detector 74 a provides a measurement of the central flux of the radiation beam and together with detectors 74 b-74 e provides indication of the variation in that flux over the area of the targets 22 and 22′ as may form the basis of a measure of flatness and symmetry. Multiple measurements from detector 74 a over time provides a measure of flux constancy.

Also positioned on the printed circuit board 70 in the detector zone 72 are energy-detectors 76 a, 76 b, and 76 c. Energy detectors 76 a, 76 b, and 76 c may be located arbitrarily within the detector zone 72 but are preferably equidistant from the detector 74 a to reduce the effects of variations of the beam profile on the their signals. These detectors directly measure radiation flux but include filters and other elements which allow the energy of the radiation beam to be determined from the flux signals. Detectors 74 and 76 will be described in more detail below.

Referring to FIGS. 4 and 5, the printed circuit board 70 positions the detectors 74 and 76 between build-up material 80 on electron-receiving face 18 of the housing 20 and build-up material 82 on the photon-receiving face 16 of housing 20. During use, therefore, electrons 84 will arrive at detectors 74 and 76 after passing through build-up material 80 and photons 87 will arrive at detectors 74 and 76 after passing through build-up material 82. Each of build-up materials 80 and 82 is optimized for the particular type of radiation it is intended to receive. In the preferred embodiment, the build-up material 80 is a plastic material equivalent to 1.5 centimeters of water optimized for electrons and a build-up material 82 is a plastic material equivalent to 3.5 centimeters of water optimized for photons. More generally, the amount of build-up material 80 and 82 is selected to increase the sensitivity of the detectors 74 and 76 to the particular mode of radiation and to provide even sensitivity of the detectors 74 and 76 (ignoring for the moment any filtration) to the expected energy range of the particular radiation mode.

Referring specifically to FIG. 5, detectors 74 a-74 d are intended to measure radiation flux directly and have no additional filtration. Energy-detectors 76 a, 76 b, and 76 c, however, have additional filter and backscatter elements to allow them to distinguish among different energies of radiation. In the preferred embodiment, detector 76 a has 10 mm of aluminum 86 on its side toward electron-receiving face 18 and energy-detector 76 b has 1 mm of aluminum 88 on its side toward electron-receiving face 18. Energy-detector 76 c, in contrast, provides no filtration material on its die toward electron-receiving face 18, but on the side closest to photon-receiving face 16 provides 6 mm of lead. This lead provides backscatter of electrons coming through electron-receiving face 18, which hit the lead 90 and scatter back into energy-detector 76. The lead may alternatively be a brass disk.

The filtration and backscatter element cause each of these energy detectors 76 a, 76 b, and 76 c to produce a slightly different signal. When combined, these signals provide a discrimination of different energies as will be described below.

Referring now to FIG. 6, in the preferred embodiment, each of detectors 74-76 is an ionization detector of a type in which ionized gas provides a path of conduction between charged and separated plates, and are manufactured using printed circuit board techniques such as those employing a photo resist/etching process or the like.

In particular, a manufacturing technique of the present invention provides circular disk-shaped collector 92 on the upper surface of the printed circuit board 70 to provide one charged plate. The collector is surrounded by a guard ring 94, which in turn is surrounded by a high voltage ring 96 leading by trace 98 to a high voltage source. The remainder of the surface of the printed circuit board 70, in near proximity to the detector 74 or 76, may include a ground plane 100.

A brass cap 102 being a hollow cylinder with an open lower base may be attached at the edge of the lower base to the high voltage ring 96 by solder, or the like. The upper solid base of the brass cap is preferably approximately 0.25 mm thick. A vent port 104 is drilled through the printed circuit board 70 to provide pressure equalization to the inner surface of the brass cap 102, which holds ionizing air at ambient pressure. Alternatively, the vent port 104 could be drilled through the brass cap 102. Other materials than brass can be used for the cap as will be understood to those of ordinary skill in the art. A chamber created within the cap and upper surface of the printed circuit board encloses approximately 0.6 cubic cm of air.

Referring to FIG. 7, the printed circuit board 70 may be a multi-layer printed circuit board having the upper layer shown in FIG. 6 providing copper cladding forming the collector 92, guard ring 94, high voltage ring 96, and ground plane 100. Beneath and supporting this upper layer is an insulator 106 and then a ground plane 108. Beneath the ground plane 108 is another insulator 110, followed by a signal plane 112 another insulator 109 and finally an outer ground plane 114. The printed circuit board 70 may be standard copper clad epoxy-impregnated fiberglass with the copper etched into the desired patterns using photo resist processes or other well known printed circuit techniques.

Generally, the signal plane 112 includes multiple traces, one connecting to collector 92 by via 116. The ground plane 100 may be joined by vias 118 and 120 to guard ring 94 and ground planes 108 and 114, the former which may provides holes through which via 116 may pass. As apparent from FIG. 7, the traces of the signal plane 112 are thus always flanked on their upper, lower, right and left surfaces by ground planes 114 and 108 providing shielding to the signals detected signals.

Referring now to FIG. 12, in an alternative embodiment, the cap 102 of FIGS. 6 and 7 may be replaced with a continuous conductive plate 170 generally parallel to and spaced in front of the printed circuit board 70 with respect to incoming radiation. The edges of the conductive plate 170 may contact and be supported by a high voltage trace 172 at the edge and on the front surface of the printed circuit board 70 so that a center portion of a single conductive plate 170 may cover multiple collectors 92 forming different detectors 74, 76. Each of the collectors 92 may be fully surrounded by a ground plane 100 being an extension of the guard ring 94 previously described. Connections of the collectors 92 to other circuitry may be provided by internal conductors as shown in FIG. 7.

The material of the conductive plate 170 is preferably a conductive polymer having a known radiation equivalence such as in air equivalence or water equivalence. This latter material may be A150 Shonka Tissue-Equivalent Plastic which simulates soft body tissue, such as muscle, with respect to photons and neutrons of a wide range of energies, and consists of polyethylene, nylon, carbon black, and calcium fluoride. It has a density of 1110 kg/m3 and shows an electrical resistance of approximately 2 ohm-meters. The former material may be C552 Shonka Air-Equivalent Plastic which consists of polyvinylidene fluoride, carbon black, and silica. It has a density of 1760 kg/m3 and shows an electrical resistance of approximately 0.03 ohm-meter.

Alternatively, the material of the conductive front plate may be D400 Polystyrene-Equivalent Plastic, a polystyrene-equivalent formulation plastic which has the same atomic composition of polystyrene with respect to all types of radiation. It has a density of 1160 kg/m3 and shows an electrical resistance in the range of 0.1 to 1 ohm-meter.

The lower surface of the conductive plate 170 is spaced away from the printed circuit board 70 to provide the necessary air gap.

Referring now to FIG. 13, in an alternative embodiment, depressions 174 may be formed in the lower surface of the conductive plate 170 above each of the collectors 92 to provide for desired focusing or other control of the field lines between the conductive plate 170 and the collectors 92. The use of a single conductive plate 170 covering multiple collectors 92 eliminates the need to run separate high-voltage lines on top of the printed circuit board possibly decreasing leakage currents.

Referring now to FIGS. 4 and 8, the traces of the signal plane 112 and the ground planes 108, 100, and 114 and high voltage traces 98 may pass out of the detector zone 72 to a circuit area 73 also on the circuit board 70 but displaced from the targets 22 and 22′ and positioned between radiation shields 124. The circuit area 73 holds processing circuitry 122 including amplifiers 126 receiving signals from the signal plane 112. The amplifiers 126 connect to a multiplexing A to D converter 128 providing digitized signals to a processor 130 via an internal bus 132.

The processor 130 accesses an internal clock and calendar and communicates with a temperature and barometric pressure sensor 134 to correct for changes of ionization detectors caused by changes in ambient atmospheric pressure and temperature (as is understood in the art), with an audible annunciator 133, the RS-232 data/power connector 44, the controls 137 of the first side wall 24 including: the alphanumeric display 26, the reset button 28 the LED 29, the radiation mode captions lamps 30, and the mode select button 32. The processing circuitry 122 of the circuit area 73 may also include power supply 136 communicating via a jack 138 with the power cord 58 shown in FIG. 2.

The processor 130 executes a program stored in memory 140 to process the signals received from the detectors 74 and 76 and to store them in memory 140 as will be described. The program accepts inputs from the temperature and barometric pressure sensor 134, the RS-232 data/power connector 44, the reset button 28, and the mode select button 32 and provides outputs to the LED 29, RS-232 data/power connector 44, the alphanumeric display 26, and the radiation mode captions lamps 30 according to the inputs and the logic of the control program described herein.

Referring now to FIGS. 2 and 11, the present invention is used in three distinct phases. In a first phase, the mobile detecting unit 12 is connected to computer 68 by cable 66 and instructed by software in the computer 68 to enter a calibrate mode as indicated by process block 150. During this calibrate mode, the mobile detecting unit 12 is exposed to radiation from a radiotherapy machine (not shown) at each energy level and for each radiation mode. The energy of radiation is identified via the operator of the computer 68 and the mode identified by the mode select button 32 and matched to an energy signature determined from the measurements of the energy detectors 76 a-76 c.

Referring momentarily to FIG. 9, for electrons, the energy signature value is determined by taking the signal from detector 76 b having 1 mm of aluminum and dividing it by the signal from detector 76 a having 10 mm of aluminum. This fraction is multiplied by the backscatter signal from detector 76 c having a backstop of 6 mm of lead to produce the electron energy signature value 156.

For photons as shown in FIG. 10, the signal from detector 76 c having the 6 mm of lead as a backstop is divided by a signal from the center detector 74 to produce a photon energy signature value 156.

It will be understood that other algebraic combinations of these multiple detectors can be used and that generally the energy may be fit to a polynomial function of the signals from detectors 76 and/or 74.

The computer 68 then compiles, per process block 152, an energy table consisting of an entry for each energy and mode providing benchmark flux measurements from each of the detectors 74 a-74 d and the energy signature value 156. The energy table is downloaded into memory 140.

Referring again to FIG. 11, in a second phase of operation, the mobile detecting unit 12 is armed automatically and the LED 29 turns green and the indicators display “RDY” for ready. Then unit 12 is placed on the radiotherapy machine in the path of the radiation with the light field of the radiotherapy machine aligned with targets 22 or 22′. The operator selects the desired radiation mode corresponding with the orientation of the mobile detecting unit 12 and begins the radiation exposure. Once armed, the processor 130 monitors the signals from the detectors 74 and 76 per decision block 158 until the signals exceed a predetermined threshold indicating radiation is present.

Once this threshold is passed, at succeeding process block 160, the energy of the radiation is determined by matching the readings from detectors 74 a and 76 a-76 c (as appropriate) to the energy signature value 156 stored in the energy table in memory 140 plus and minus a predetermined range. If the energy readings do not match with any energy signature value 156 stored in the energy table, the alphanumeric display 26 shows an error message (“ERR”) and the LED 29 flashes red and there is an audible beep produced by an annunciator 133. No further readings can be taken until the reset button 28 is pressed whereupon the LED 29 returns to its default color of green.

Once the energy level of radiation has been determined, the processor 130 compares the benchmark flux measurements associated with the particular entry of the energy table, per decision block 162, to the signals from the detectors 74 a-74 d. The flatness and the symmetry of the current flux of the radiation beam is compared to a predetermined threshold value based on the benchmark flux measurements and the constancy of the flux is compared to a predetermined acceptable range also based on the benchmark flux values. Flatness is generally determined by finding the maximum and minimum values of the detectors 74 a-74 e (values of detectors indicated in the following by the detector number). Then, flatness=(Max (detectors 74 a-74 e)-Min (detectors 74 a-74 e) /(Max (detectors 74 a-74 e)+Min (detectors 74 a-74 e)). Symmetry is determined by axial=(top (detector 74 b)-bottom (detector 74 c))/bottom (detector 74 c) and transverse=(right (detector 74 d)-left (detector 74 e))/left (74 e). Constancy is determined by the center detector value over time: (detector 74 a (at time x)-detector 74 a (at benchmark time))/detector 74 a (at benchmark time).

If the current flatness, symmetry of constancy is outside of a predetennined range related to the benchmark value, an error signal is indicated per process block 164 and the alphanumeric display 26 shows an error message (“ERR”) alternating with the type of error (“SYM”,“FLT”,and “CST” for symmetry, flatness and constancy, respectively) and the LED 29 shows red and flashes together with an audible beep by the annunciator. No further readings can be taken until the reset button 28 is pressed whereupon LED 29 returns to its default color of green.

If the flux measurements are within the acceptable predetermined range, the alphanumeric display 26 shows and indicates the deduced energy level, and the unit resets itself. At process block 166, the flux values are stored in memory together with a date stamp maintained by the processor 130 as linked to the determined energy level.

The operator may then proceed through energy ranges and modes stopping only as necessary to flip the mobile detecting unit 12 according to the mode. When the measurements have been made, the operator may install the detecting unit 12 back on the cradle 14 and download the data to the computer 68 for additional analysis or preparation of automatic reports. The memory 140 is sized to hold up to thirty days worth of data so that downloading may be postponed as desired on any given day.

The third phase of operation is a wired version of phase two for real-time data collection. In this phase, the same functionality exists as is phase two, but beam checker 10 is hardwired either through the cradle 14 or directly to a remote computer 68 allowing real-time data collection and beam checker controls.

It is specifically intended that the present invention not be limited to the embodiments and illustrations contained herein, but include modified forms of those embodiments including portions of the embodiments and combinations of elements of different embodiments as come within the scope of the following claims. 

1. An ionization detector comprising: a front and rear plate positioned on a front and rear side of a volume of ionizable fluid to receive a voltage there across to thereby collect charges resulting from radiation ionizing the fluid; wherein the rear plate is formed of a printed circuit board providing a collector on its front surface and multiple layers including a middle layer providing at least one signal trace and a first and second ground layer flanking the signal trace layer; and wherein the signal trace connects to the collector.
 2. The ionization detector of claim 1 wherein the printed circuit board further provides a guard ring surrounding the collector on the front surface and wherein at least one of the ground layers connects to the guard ring.
 3. The ionization detector of claim 2 wherein the printed circuit board further provides a high voltage feed outside of the guard ring and communicating with the front plate.
 4. The ionization detector of claim 3 wherein the front plate is supported by the printed circuit board at the high voltage feed.
 5. The ionization detector of claim 3 wherein the collector and the guard ring are a disk and concentric ring, respectively, and the front plate is a cup inverted over the guard ring and collector.
 6. The ionization detector of claim 1 wherein the printed circuit board is copper clad epoxy-impregnated fiberglass.
 7. The ionization detector of claim 1 further including a port to equalize pressure inside and outside the volume.
 8. The ionization detector of claim 1 wherein the signal trace connects to the collector by a conductive via.
 9. The ionization detector of claim 1 wherein the printed circuit board further includes signal-processing circuitry receiving the signal trace.
 10. The ionization detector of claim 1 wherein the rear plate provides multiple electrically independent collectors on its front surface; and wherein a single front plate covers the multiple electrically independent collectors.
 11. The ionization detector of claim 10 wherein the single front plate is a conductive plastic material.
 12. The ionization detector of claim 11 wherein the single front plate is a tissue equivalent plastic material.
 13. The ionization detector of claim 11 wherein the single front plate is a air equivalent plastic material.
 14. The ionization detector of claim 11 wherein the single front plate is a styrofoam equivalent plastic material.
 15. The ionization detector of claim 10 wherein the single front plate includes depressions positioned at the multiple electrically independent collectors.
 16. The ionization detector of claim 10 wherein the single front plate is spaced from the rear plate in a region of the collectors. 